WO2009054706A2 - Appareil et procédé de création d'image doppler de tissu à l'aide d'une image de synthèse - Google Patents

Appareil et procédé de création d'image doppler de tissu à l'aide d'une image de synthèse Download PDF

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Publication number
WO2009054706A2
WO2009054706A2 PCT/KR2008/006319 KR2008006319W WO2009054706A2 WO 2009054706 A2 WO2009054706 A2 WO 2009054706A2 KR 2008006319 W KR2008006319 W KR 2008006319W WO 2009054706 A2 WO2009054706 A2 WO 2009054706A2
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WO
WIPO (PCT)
Prior art keywords
tdi
increment
auto correlation
scan line
decrement
Prior art date
Application number
PCT/KR2008/006319
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English (en)
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WO2009054706A3 (fr
Inventor
Moo Ho Bae
Jeong Ho Ham
Original Assignee
Medison Co., Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Medison Co., Ltd. filed Critical Medison Co., Ltd.
Priority to US12/739,319 priority Critical patent/US9360552B2/en
Priority to EP08842438.7A priority patent/EP2203120B8/fr
Priority to JP2010530936A priority patent/JP5470260B2/ja
Publication of WO2009054706A2 publication Critical patent/WO2009054706A2/fr
Publication of WO2009054706A3 publication Critical patent/WO2009054706A3/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8979—Combined Doppler and pulse-echo imaging systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A—HUMAN NECESSITIES
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A61B8/5276—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts due to motion
    • G—PHYSICS
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    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8997—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using synthetic aperture techniques
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52023—Details of receivers
    • G01S7/52025—Details of receivers for pulse systems
    • G01S7/52026—Extracting wanted echo signals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
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    • G01S7/52023—Details of receivers
    • G01S7/52025—Details of receivers for pulse systems
    • G01S7/52026—Extracting wanted echo signals
    • G01S7/52028—Extracting wanted echo signals using digital techniques
    • G—PHYSICS
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    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
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    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/488—Diagnostic techniques involving Doppler signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/56—Details of data transmission or power supply
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G01S7/52047—Techniques for image enhancement involving transmitter or receiver for elimination of side lobes or of grating lobes; for increasing resolving power
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G01S7/52049—Techniques for image enhancement involving transmitter or receiver using correction of medium-induced phase aberration
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52077—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging with means for elimination of unwanted signals, e.g. noise or interference
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
    • G01S7/52095—Details related to the ultrasound signal acquisition, e.g. scan sequences using multiline receive beamforming

Definitions

  • the present invention generally relates to an apparatus and method for creating a tissue Doppler image, and more particularly to an apparatus and method for forming a tissue Doppler image using a synthetic image.
  • the image processing system which is used for processing and displaying an image of a target object, is applied in various fields.
  • the image processing system may include an image processing system for ultrasound diagnosis (hereinafter referred to as “ultrasound diagnostic system").
  • the ultrasound diagnostic system transmits an ultrasound signal from the surface of a human body toward a desired portion within a target object. This is so that an ultras ound image of soft tissues or blood flow can be obtained through non-invasive means by using information obtained through ultrasound echo signals.
  • the ultrasound diagnostic system is advantageous since it is small in size and fairly inexpensive. Further, the ultrasound diagnostic system is capable of providing real-time display and is highly safe without any dangerous side effects such as exposure to X-rays, etc. Thus, it is extensively utilized for diagnosing the heart, abdomen and urinary organs, as well as being widely applied in the fields of obstetrics, gynecology, etc.
  • Reflectivity of the ultrasound signals is different from a blood flow and a myocardium.
  • the reflectivity of the ultrasound signal at the blood flow is relatively low while its moving velocity is more rapid than a myocardial velocity.
  • the myocardial velocity is relatively slow, the reflectivity of the ultrasound signal is very high.
  • a tissue Doppler image (TDI) indicating the measured myocardial velocity may be used to evaluate a myocardial function.
  • the TDI may transmit ultrasound signals along one scan line with an identical acoustic field at a constant time interval and detect a phase shift of received ultrasound signals to thereby compute a mean Doppler frequency by using auto correlation. This is so that a color image of a target object may be displayed.
  • the TDI may be applicable for assessing objective systolic and diastolic myocardial velocities, determining regional dysfunction and quantitatively assessing the myocardial velocities. This is such that the TDI may be helpful in following up cardiac functions from congenital and acquired cardiac diseases.
  • TDI receive scan lines are required by an ensemble number necessary for calculation. Further, auto correlation is performed upon receive signals to form the TDI. That is, the ultrasound signal is repeatedly transmitted to one scan line by the ensemble number N (e.g., N ultrasound transmissions to a first scan line, N ultrasound transmissions to a second scan line, N ultrasound transmissions to a third scan line ). Then, the received signals are synthesized to produce the TDI. For example, assuming that 10 scan lines are required for one TDI, the ultrasound signal should be repeatedly transmitted to each of the scan lines by the ensemble number N (10 N ultrasound transmissions) such that a long time for producing the TDI is required.
  • the ensemble number N 10 N ultrasound transmissions
  • a frame rate is determined depending on a region of interest, an ensemble number, an interleaving number and the like.
  • a delay is increased with increasing the ensemble number.
  • the frame rate is also decreased. Disclosure of Invention
  • an apparatus and method capable of producing a tissue Doppler image without repeatedly transmitting ultrasound signals by the ensemble number to each scan line.
  • an ultrasound beam is transmitted in a non- sequential manner.
  • a plurality of receive beams received in response to each transmission of the transmit beam are grouped into an increment data group of a scan line index increasing direction and a decrement data group of a scan line index decreasing direction.
  • Auto correlation is performed for the increment and decrement data groups of the scan line increasing and decreasing directions.
  • weights are applied to respective auto correlation values for the increment and decrement data group, and the auto correlation values with the weight applied are summed to compute a mean phase.
  • At least one of velocities, powers, variances in response to the mean phase is outputted to produce TDI.
  • the non-sequential manner is achieved by setting a plurality of scan lines, defining sequential indices of the scan lines, setting an order of the transmit beam for the scan lines in a non- sequential manner in which increment and decrement of the indices are repeated, and transmitting the transmit beam according to the set transmit order.
  • a plurality of receive beams corresponding to each transmission of the transmit beam transmitted according to the transmit order are obtained.
  • the receive beams are then grouped to an increment data group of a scan line index increasing direction and a decrement data group of a scan line index decreasing direction.
  • the auto correlation is carried out for the increment and decrement data groups of the scan line increasing and decreasing directions, and weights are applied to respective auto correlation values for the increment and decrement data group. Thereafter, the auto correlation values with the weight applied are summed to compute the mean phase.
  • a TDI may be produced without lowering a frame rate compared to the conventional method, while the ultrasound signals are not repeatedly transmitted by the ensemble number to each scan line. Also, since the side lobe levels are removed, there is a merit in that the TDI can be produced by using data corresponding to different transmit scan lines as an ensemble.
  • FIG. 1 is a schematic diagram showing a process of forming a general synthetic ima ge-
  • FIG. 2 is a schematic diagram showing examples of ultrasound radiation.
  • FIG. 3 is a schematic block diagram illustrating an ultrasound diagnostic system adopting a tissue Doppler image producing apparatus in accordance with one embodiment of the present invention.
  • FIG. 4 is a schematic block diagram illustrating a beam former and an echo processing unit.
  • FIG. 5 is a schematic block diagram illustrating an image motion estimation/compensation control unit.
  • FIG. 6 is an exemplary diagram showing a transmit order of a transmit beam.
  • FIG. 7 is a schematic diagram showing an example of a synthetic aperture imaging method by using BiPBF.
  • FIG. 8 is a schematic diagram showing a relation between low resolution images and scan lines.
  • the image When an image is obtained by using an array transducer in an ultrasound diagnostic system, the image may be obtained through one transmission and reception in response thereto. However, scan lines neighboring the scan lines, which have been already received, take part in forming an ultrasound synthetic image. That is, the ultrasound synthetic image may be formed by using multi-receive beams in response to one time transmission of a transmit beam. For example, in order to obtain an n scan line S , n transmission and reception are typically carried out along the scan line S to obtain an n image.
  • an ultrasound image may be formed by combining neighboring scan lines S n-m , S n-(m-l) , ..., S n , ..., S n+(m-l) , S n+m , wherein m>0, for the scan line S n .
  • P s represents an overlapping portion of wave fronts of waves transmitted along three scan lines, e.g., scan lines S n-l , S n and S n_l
  • the overlapping portion is considered to obtain an ultrasound image.
  • a target object When a target object is a stationary object, an ultrasound synthetic image having good resolution and a signal to noise ratio (SNR) may be obtained.
  • SNR signal to noise ratio
  • the target object when the target object is a moving object (especially moving in an axial direction), an undesirable image may be displayed in an ultrasound synthetic image. That is, one scan line in the ultrasound synthetic image may be formed by using multi-receive beams obtained with a time delay or multi-receive beams responsive to one transmission beam such as bi-directional pixel based focusing (BiPBF).
  • BiPBF bi-directional pixel based focusing
  • An image synthesizing process using BiPBF which is one of transmit synthetic- aperture focusing methods capable of increasing a transmit power of the ultrasound signal by using signals from a plurality of transmit fields, may perform transmit and receive focusing for all points.
  • a transmit focal point may be translated by referring to a virtual source element.
  • 2a shows a transmit field in a brightness (B) mode. As shown in 2a of FIG. 2,
  • beams which are radiated from the array transducer, converges toward a focal point and then diverges in the shape of a circular wave within a limited angular extent.
  • a virtual source element which is one of the array transducers, is located at a focal depth.
  • the virtual source element may generate a circular wave back and forth with respect to itself.
  • transmit fields of two virtual source elements are overlapped at imaging points. One imaging point is shown before the focal depth and the other imaging point is shown after the focal depth with respect to a center of symmetry of the circular field.
  • the image synthesizing process using BiPBF may be able to maintain a uniform lateral resolution over all focal depths and reduce a side lobe level compared to other methods. Also, since the transmit power increases due to the synthesis of transmit fields, an ultrasound synthetic image having an enhanced SNR may be obtained through the image synthesizing process using BiPBF. However, the image synthesizing process using BiPBF may be restricted to imaging a stationary or slowly moving object. If the image synthesizing process using BiPBF is applied for imaging a fast moving object, then the resolution may be degraded or the target object may disappear in the ultrasound synthetic image. Especially, a motion occurring in an axial direction may largely affect the ultrasound synthetic image compared to a motion occurring in a lateral direction.
  • the ultrasound synthetic image based on BiPBF for the stationary target object has a relatively better image quality compared to an image based on the single transmission/reception method
  • the ultrasound synthetic image based on BiPBF for the moving target object may have a worse image quality than an image based on the single transmission/receptionmethod.
  • the present invention may produce the TDI by applying the ultrasound synthetic imaging process using BiPBF without repeatedly transmitting the ultrasound signal by the ensemble number to each scan line (a synthetic imaging processing is adopted rather than the single transmission/reception method). Especially, the present invention may remove an effect of the side lobe in the synthetic image and estimate and compensate a motion to thereby produce the TDI. This is so that the TDI may be produced without lowering the frame rate while the ultrasound signal is not transmitted by the ensemble number to each scan line. Also, since the side lobe levels are removed, there is a merit in that the TDI can be produced by using data corresponding to different transmit scan lines as an ensemble.
  • the 2D-TDI may repeatedly transmit an ultrasound signal with an identical acoustic field at a constant time interval and detect a phase shift of echo signals to thereby find a mean Doppler frequency by using auto correlation or other methods.
  • the synthetic aperture imaging may be similar to the 2D-TDI in terms of repeatedly transmitting an ultrasound signal. However, the SAI may transmit an ultrasound signal in a different acoustic field per transmission, which is different from the 2D-TDI.
  • a wave front of the acoustic field may be rotated in a constant angle per transmit in view of each of the pixels. This rotation may cause the side lobes in a low resolution image formed based on each transmission to be also rotated.
  • a motion in an axial direction may be found to be similar to a tissue Doppler.
  • the present invention adopts a new transmit order of a transmit beam (e.g., non-sequential transmission of a transmit beam) for compensating for the wrongly detected motion and provides a phase detecting method through auto correlation to estimate and compensate the motion, so that the side lobes may be removed.
  • the TDI may be produced by using data of transmit scan lines in different locations as an ensemble.
  • FIG. 3 is a schematic block diagram illustrating an ultrasound diagnostic system using a tissue Doppler image producing device in one embodiment.
  • FIG. 4 is a block diagram illustrating a beam former 30 and an echo processing unit 41.
  • FIG. 5 is a schematic block diagram illustrating an image motion estimation/compensation control unit 31.
  • a transmit/receive unit 10 may include a probe (not shown) containing an array transducer.
  • the probe may be configured to transmit and receive ultrasound signals.
  • the transmit/receive unit 10 may further include a transmitter (not shown) and an analog receiver (not shown).
  • the array transducer may comprise a plurality of elements (e.g., 128 elements) and may be configured to output the ultrasound pulses in response to transmit pulses applied from the transmitter.
  • the analog receiver may receive reflection signals (echo signals), which are the ultrasound pulses outputted from the respective elements of the array transducer reflected from the target object.
  • the analog receiver may be configured to amplify the reflection signals, remove aliasing phenomenon and noises, and compensate for attenuation occurring while the ultrasound pulses are propagated into the target object.
  • a transmit/receive switch 20 may switch transmission and reception of the ultrasound signals for the same elements.
  • the transmit/receive switch 20 may be further configured to prevent a high power outputted from the transmitter from affecting the analog receiver. That is, when the transmission and reception are alternately carried out, the transmit/receive switch 20 may be configured to appropriately switch the transmitter and the analog receiver.
  • a beam former 30 may be configured to perform receive focusing upon signals received at the respective transducer elements.
  • the beam former 30 may include a gain adjusting unit 301, an analog-to-digital converting unit 302, a delay unit 303, an image synthesizing unit 304 and a summing unit 305.
  • the gain adjusting unit 301 may be configured to compensate gain of the analog receive signals received at the analog receiver.
  • the analog-to-digital converting unit 302 may be configured to convert the analog receive signals to digital receive signals.
  • the delay unit 303 may apply a different amount of delay, which depends on positions for receive focusing, to the digital receive signals (determined based on distance differences between the respective elements and a focal point).
  • the image synthesizing unit 304 may be configured to synthesize the delayed signals to thereby form a receive-focused beam.
  • the summing unit 305 may be configured to sum the receive-focused beams formed at respective channels.
  • An echo processing unit 40 may be configured to convert the radio frequency (RF) receive-focused beam into a baseband signal and perform envelop detection with a quadrature demodulator, thereby obtaining an ultrasound image data corresponding to scan lines.
  • RF radio frequency
  • a scan converting unit 50 may store the receive-focused data from a predetermined point on the scan line and scan-convert the receive-focused data in a format capable of being displayed on a display unit 60. That is, the scan converting unit 50 may be configured to convert the ultrasound image data in an appropriate data format capable of being displayed.
  • the display unit 60 may display an image-processed ultrasound image.
  • the TDI producing apparatus in one embodiment may provide a specified sequence of the ultrasound transmit beam (i.e., transmission in a non- sequential transmit order) and generate data necessary for motion estimation and compensation (e.g., phase and power data formed in a pixel unit or a sample unit) by inputting data grouping receive beams in response to the ultrasound transmit beam into auto correlators 311-313.
  • the TDI producing apparatus may compute data required for producing the TDI, i.e., velocities, powers and variances.
  • a transmit/receive control unit 21 may control the transmit/receive switch 20 such that the transmit beam is non- sequentially transmitted (see FIG. 6).
  • the transmit/receive control unit 21 may group data of a scan line index increasing direction and data of a scan line index decreasing direction to increment group data and decrement group data, respectively, for the receive beams received in response to the transmission of the transmit beam of the non- sequential manner.
  • the transmit/receive control unit 21 may control M and N numbers of increment group data of the scan line index increasing direction and L numbers of decrement group data of the scan line index decreasing direction to be inputted to auto correlators (311-313 in FIG. 5), respectively.
  • the auto correlators 311-313 of the image motion estimation/compensation control unit 31 may extract phase and power data for the motion of the target object by using the increment group data of the scan line index increasing direction and the decrement group data of the scan line index decreasing direction.
  • a summation unit 314 may sum the phase and po was data of the increment and decrement groups and transfer the summed data to the control unit 315.
  • the control unit 315 may generate pixel or sample based mean phase and power data for the increment/decrement group data.
  • the pixel or sample based mean phase and power data are transferred to the echo processing unit.
  • These pixel or sample based mean phase and power data are data for producing TDI.
  • the echo processing unit 40 may output a velocity, a power and a variance for the mean phase and power data through a mapper 41.
  • the mapper 41 of the echo processing unit 40 may store velocities, powers and variances for the mean phase and power data.
  • the mapper 41 may automatically output one of the velocities, one of the powers or one of the variances in response to the input of the mean phase and power data. Further, the mapper 41 may automatically output at least two velocities, powers or variances corresponding to the mean phase and power data.
  • the mapper 41 may further perform post-processing functions, i.e., functions for an enhanced color display (e.g., flash rejection, etc.).
  • a scan converting unit 50 may convert the ultrasound scan line signals transferred from the mapper 41 into monitor scan line signals so that the TDI may be displayed on a display unit 60. In such a case, the TDI displayed on the display unit 60 is a color image having high resolution for the moving target object like the stationary object.
  • the TDI may be displayed as 2D-TDI or 3D-TDI.
  • the TDI may be displayed together with the B-mode image formed through the ultrasound synthetic process.
  • the non- sequential manner is achieved by setting a plurality of scan lines (e.g., 9 scan lines) for the ultrasound synthetic image, defining sequential indices of the scan lines (e.g., index 0, index 1, index 2, ..., index 9), setting an order of the transmit beam for the scan lines in a non-sequential manner in which increment and decrement of the indices are repeated (e.g., index 1, index 0, index 3, index 2, index 5, index 4,...) and transmitting the transmit beam according to the set transmit order.
  • a plurality of scan lines e.g., 9 scan lines
  • defining sequential indices of the scan lines e.g., index 0, index 1, index 2, ..., index 9
  • an order of the transmit beam for the scan lines in a non-sequential manner in which increment and decrement of the indices are repeated (e.g., index 1, index 0, index 3, index 2, index 5, index 4,...) and transmitting the transmit beam according to the set transmit order.
  • the ultrasound beam is transmitted in a non-sequential manner and a plurality of receive beams received in response to each transmission of the transmit beam are grouped into an increment data group of a scan line index increasing direction and a decrement data group of a scan line index decreasing direction.
  • Auto correlation is performed for the increment and decrement data groups of the scan line increasing and decreasing directions, weights are applied to respective auto correlation values for the increment and decrement data group, and then the auto correlation values with the weight applied are summed. This is so that the effect of the side lobe may be removed.
  • the summation value may become zero for the stationary object. However, the summation value may not be zero for the moving object. This value may be the mean phase and power of the moving object.
  • the image motion estimation/compensation control unit 31 may exist in an exterior separated from the beam former 30.
  • the position of the image motion estimation/compensation control unit 31 may not be limited thereto.
  • a phase of a main lobe and a side lobe in an ultrasound synthetic image for a stationary object and an ultrasound synthetic image for a moving object will be checked through the low resolution images (LRI). Then, the phase will be re-checked after setting a new transmit order of the transmit beams for the scan lines.
  • LRI low resolution images
  • FIG. 7 is a schematic diagram showing an example of a synthetic aperture imaging method by using the BiPBF.
  • N may be an ensemble number necessary for computing the mean phase and powers by using auto correlation function. It may be assumed that 0-8 wave fronts (data order inputted to auto correlation function, i.e., ensemble index) may be overlapped at an arbitrary point P for image synthesis.
  • the scan line may be increased by 0-8.
  • Sy nthetic images may be configured by gathering respective index 0, index 1..., index 8.
  • an LRI corresponding to the index 4 is a typical image obtained by one transmission and one reception.
  • an image for a main lobe may be indicated in the shape of a black hole as an auto correlation result since the phases for the main lobe are not changed.
  • a phase may be changed due to the side lobe in spite of the stationary object.
  • the phase shift becomes lower with closing to the main lobe.
  • the phase shift due to the side lobe should be minimized regardless of the stationary or movement of the target object. If the motion is computed by auto correlation without considering the side lobes, then it may be determined that the stationary object is moved in addition to the moving object.
  • an auto correlation procedure for the receive beams obtained through the transmission in the non-sequential manner to the stationary object or a moving object will be described in detail.
  • the moving velocity should be 0 m/s in case of the stationary target object.
  • a velocity component may be detected due to the effect of the side lobe. That is, if the transmit beam is transmitted in a sequential order for the stationary object, then a phase for the main lobe is not changed. However, a phase for the side lobe is rotated in a constant pattern in an x-y space. In such a case, the motion compensation may not be correct. Further, an accurate phase for the moving object should be estimated for the compensation.
  • the present invention may transmit the transmit beam in a nonsequential manner (not in a sequential manner) to minimize the effect of the side lobes and then perform the auto correlation for the receive beams obtained in response to the transmission.
  • FIG. 6 is a schematic diagram showing an example of the transmit beam transmitted in a non- sequential manner.
  • the scan lines may be divided into an increment group of a scan line index increasing direction and a decrement group of a scan line index decreasing direction, wherein the increment is +2 and the decrement is -1, which are different from each other.
  • the transmission is carried out not in an order of neighboring scan lines such as 1, 2, 3, 4 ...., but rather in an order of 2, 1, 4, 3, 6, 5 ... (non- sequential transmission) such that the increment and decrement of the scan line index, which are -1 and +2, are to be repeated.
  • a mean phase difference calculated from a(2, 4), a(3, 5), a(8, 10), etc. i.e., B group having a number difference of +2 for pixels located in the side lobe of the stationary target object
  • B a mean phase difference calculated from a(2, 1), a(4, 3), a(6, 5), etc (i.e., A group having a number difference of -1)
  • A the mean phase differences for the stationary target object are denoted as A and B, then the following equation (1) may be approximately obtained.
  • the mean phase may be calculated by using the auto correlation.
  • the auto correlation may be carried out as follows.
  • Function z (t) may be defined by functions z(t) and z (t-T) as the following equation (4)
  • n represents the number of the consecutive transmit pulses in a constant direction, which is referred to as an ensemble number in an ultrasound image.
  • Equation 7 represents an auto correlation function for the receive beams corresponding to the increment group having the increment of +2.
  • equations (8) and (9) represent the power and phase of the increment group of the scan line index increasing direction. This process is carried out by an auto correlator 312 for the increment group of the scan line index increasing direction among the auto correlators 311-313 of the image motion estimation/compensation control unit 31.
  • Equation (13) may represent auto correlation function for the part of decreasing the transmit scan line arrangement by -1.
  • Equations (14) and (15) may represent a power and a phase of the decrement group of the scan line index decreasing direction. This process may be carried out in the auto correlator 311 for the decrement group of the scan line index decreasing direction among the auto correlators 311-313 of the image motion estimation/compensation control unit 31.
  • R 1x (Tj) R su (T n 0 + R ⁇ T D ,t)
  • Equation (18) may represent a pixel based mean power. Further, equation (19) represents a pixel based mean phase. By using this, a specific area based means power and mean phase can be obtained. As such, the result of equations (16) and (17) may be expressed in space coordinates as the following equation (20).
  • Equation 21 The equation (20) may be expressed as the following equations (21) and (22) so that it can be extended to a type having a specific area based mean phase. [106] [Equation 21]
  • the power may be computed together with the phase as the above equations to increase a degree of freedom of the compensation based on the power in the motion estimation and compensation. For example, when the power threshold is a reference, a much lower power may be ignored.
  • TDI may be produced without the time delay while the ultrasound signals are not repeatedly transmitted by the ensemble number for each scan line.
  • the TDI may be produced by using data of transmit scan lines in different locations as an ensemble due to the removal of the side lobe level.
  • the transmit beam is transmitted in a non- sequential manner to the stationary object or the moving object, as shown in FIG. 6.
  • an effect of the side lobe affecting the main lobe may be considerably reduced.
  • the effect of the side lobe may be reduced by adjusting the power threshold voltage.
  • the present invention may be applicable to an ultrasound diagnostic system.

Abstract

L'invention concerne un appareil et un procédé permettant de produire une image Doppler de tissu sans émission répétée de signaux ultrasonores sur chaque ligne de balayage. Conformément à la présente invention, un faisceau ultrasonore est émis de manière non séquentielle et une pluralité de faisceaux de réception reçus en réponse à chaque émission du faisceau d'émission est regroupée en un groupe de données d'incrémentation d'un sens croissant d'indice de ligne de balayage et en un groupe de données de décrémentation d'un sens décroissant d'indice de ligne de balayage. Une corrélation automatique est mise en oeuvre pour les groupes de données d'incrémentation et de décrémentation des sens croissant et décroissant de ligne de balayage, des pondérations sont appliquées aux valeurs de corrélation automatique respectives pour les groupes de données d'incrémentation et de décrémentation, puis les valeurs de corrélation automatique sur lesquelles la pondération est appliquée sont sommées afin de calculer une phase moyenne. Des vitesses, des puissances et/ou des variances sont émises en réponse à la phase moyenne afin de produire une TDI.
PCT/KR2008/006319 2007-10-25 2008-10-24 Appareil et procédé de création d'image doppler de tissu à l'aide d'une image de synthèse WO2009054706A2 (fr)

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US12/739,319 US9360552B2 (en) 2007-10-25 2008-10-24 Apparatus and method for creating tissue doppler image using synthetic image
EP08842438.7A EP2203120B8 (fr) 2007-10-25 2008-10-24 Appareil et procédé de création d'image doppler de tissu à l'aide d'une image de synthèse
JP2010530936A JP5470260B2 (ja) 2007-10-25 2008-10-24 合成映像を用いた組織ドップラ映像形成装置および方法

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Families Citing this family (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005051781A1 (de) * 2005-10-28 2007-05-03 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Verfahren zur zerstörungsfreien Untersuchung eines Prüfkörpers mittels Ultraschall
EP2053420B1 (fr) * 2007-10-25 2012-12-05 Samsung Medison Co., Ltd. Procédé de suppression d'un effet de lobes latéraux dans la formation d'une image synthétique à ultrasons par estimation et compensation de l'influence de mouvement
KR101798081B1 (ko) 2011-04-20 2017-11-15 삼성전자주식회사 진단영상을 생성하는 방법, 이를 수행하는 장치, 진단시스템 및 의료영상시스템
KR101792589B1 (ko) 2011-04-26 2017-11-01 삼성전자주식회사 빔포머, 진단시스템, 의료영상시스템 및 진단영상을 표시하는 방법
KR101356616B1 (ko) * 2012-02-17 2014-02-04 알피니언메디칼시스템 주식회사 가중치 보간 방법 및 이를 이용한 초음파 진단장치
JP6285241B2 (ja) * 2014-03-26 2018-02-28 富士フイルム株式会社 音響波処理装置、音響波処理装置の信号処理方法およびプログラム
KR101569673B1 (ko) * 2014-10-14 2015-11-18 대진대학교 산학협력단 초음파 영상의 부엽 저감 방법
KR101631466B1 (ko) * 2014-12-10 2016-06-27 대진대학교 산학협력단 불균일 산란체 영상 획득을 위한 초음파 영상 처리장치 및 방법
KR102387708B1 (ko) 2015-01-30 2022-04-19 삼성메디슨 주식회사 향상된 hprf 도플러 영상을 위한 가이드를 제공하는 방법 및 초음파 시스템
KR101643304B1 (ko) 2015-08-20 2016-07-28 대진대학교 산학협력단 비선형 필터를 이용한 초음파 영상의 부엽 저감장치
JP6665614B2 (ja) 2016-03-18 2020-03-13 コニカミノルタ株式会社 超音波信号処理装置、超音波信号処理方法、及び、超音波診断装置
KR101809358B1 (ko) * 2016-03-30 2017-12-14 서강대학교산학협력단 새로운 평면파 합성을 이용한 초음파 도플러 영상 장치 및 그 제어 방법
US10571554B2 (en) * 2016-11-29 2020-02-25 Siemens Medical Solutions Usa, Inc. Adaptive post beamformation synthetic aperture for ultrasound imaging
KR101858137B1 (ko) * 2017-03-08 2018-05-16 대진대학교 산학협력단 컴퓨터 시뮬레이션을 이용한 초음파 영상의 부엽 억제 필터 평가 방법
US11647989B2 (en) * 2018-09-11 2023-05-16 Philips Image Guided Therapy Corporation Devices, systems, and methods for multimodal ultrasound imaging
KR102115446B1 (ko) 2019-01-04 2020-05-27 대진대학교 산학협력단 의료용 초음파 영상에서 질량중심 위치의 가중치 연산을 이용하여 부엽을 억제하는 방법
KR20230163067A (ko) 2022-05-23 2023-11-30 대진대학교 산학협력단 의료용 초음파 영상 시스템에서 부엽과 격자엽을 억제하는 방법

Family Cites Families (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2772048B2 (ja) * 1988-07-13 1998-07-02 株式会社東芝 超音波診断装置
US4972838A (en) * 1988-07-13 1990-11-27 Kabushiki Kaisha Toshiba Ultrasonic diagnostic apparatus
JPH078492A (ja) * 1993-06-28 1995-01-13 Toshiba Corp 超音波診断装置
JP3462584B2 (ja) * 1994-02-14 2003-11-05 フクダ電子株式会社 超音波診断装置
JP4350771B2 (ja) 1994-07-22 2009-10-21 株式会社東芝 超音波診断装置
US5438994A (en) * 1994-10-07 1995-08-08 Advanced Technology Laboratories, Inc. Ultrasonic diagnostic image scanning
US5738098A (en) * 1995-07-21 1998-04-14 Hewlett-Packard Company Multi-focus ultrasound lens
JP3707882B2 (ja) * 1995-11-21 2005-10-19 株式会社東芝 超音波診断装置
JPH10127634A (ja) 1996-11-06 1998-05-19 Aloka Co Ltd 超音波診断装置
KR100232257B1 (ko) * 1997-09-04 1999-12-01 이민화 클러터신호의 과도응답을 최소로 하는 초음파칼라도플러영상시스템
JPH11164833A (ja) * 1997-09-30 1999-06-22 Toshiba Corp 医用画像診断装置
US5961462A (en) 1998-05-18 1999-10-05 Atl Ultrasound Ultrasonic doppler imaging at high frame rates of display
US6352508B1 (en) 1998-11-20 2002-03-05 Acuson Corporation Transducer motion compensation in medical diagnostic ultrasound extended field of view imaging
US6193662B1 (en) * 1999-02-17 2001-02-27 Atl Ultrasound High frame rate pulse inversion harmonic ultrasonic diagnostic imaging system
KR100352639B1 (ko) * 1999-05-06 2002-09-18 주식회사 메디슨 칼라 도플러 영상화 시스템을 위한 칼라 영상 표시방법 및 장치
US6352507B1 (en) * 1999-08-23 2002-03-05 G.E. Vingmed Ultrasound As Method and apparatus for providing real-time calculation and display of tissue deformation in ultrasound imaging
US6186950B1 (en) * 1999-11-04 2001-02-13 Atl Ultrasound Ultrasonic pulse inversion harmonic separation with reduced motional effects
US6514206B2 (en) * 2001-03-09 2003-02-04 Koninklijke Philips Electronics, N.V. Simultaneous fundamental and harmonic ultrasonic imaging
US20080139938A1 (en) * 2002-06-07 2008-06-12 Fuxing Yang System and method to identify and measure organ wall boundaries
JP4011463B2 (ja) * 2002-11-07 2007-11-21 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー 超音波診断装置
JP4504004B2 (ja) * 2003-12-17 2010-07-14 株式会社東芝 超音波診断装置
JP2006223736A (ja) * 2005-02-21 2006-08-31 Toshiba Corp 超音波診断装置
KR20080059399A (ko) * 2005-10-27 2008-06-27 코닌클리케 필립스 일렉트로닉스 엔.브이. 심장 재동기 요법을 위한 더 좋은 도플러 조직 이미지 처리파형을 생성하기 위한 조직 가속도의 사용
US7965413B2 (en) * 2007-03-29 2011-06-21 Xerox Corporation Method and system for detection of binary halftone frequencies

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
None
See also references of EP2203120A4

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WO2009054706A3 (fr) 2009-07-23
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KR20090042183A (ko) 2009-04-29
EP2203120B8 (fr) 2013-09-04
EP2203120A4 (fr) 2012-06-20
JP5470260B2 (ja) 2014-04-16
KR20090042152A (ko) 2009-04-29
EP2203120A2 (fr) 2010-07-07
JP2011500261A (ja) 2011-01-06
KR100971433B1 (ko) 2010-07-21
US20100234729A1 (en) 2010-09-16
KR20090042185A (ko) 2009-04-29

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